Apparatus and method to provide breathing support

ABSTRACT

A ventilator, or a breathing assistance apparatus, is provided to ventilate patients who may have breathing difficulties, said device comprising a inspiratory pressure control duct; a positive end-expiratory pressure control duct; at least one valve connected to the peak inspiratory pressure control duct and to the positive end-expiratory pressure control duct, and at least one controller communicably connected to the valve to control rate of cycling of the valve, thereby controlling number of breaths per minute, and to control the duration of peak inspiratory pressure also known as inspiratory time.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation-in-part of co-pending U.S patentapplication Ser. No. 14/468,320, filed Aug. 25, 2014; which claims thebenefit of the earlier filing dates of U.S. Provisional PatentApplication No. 61/874,323, filed Sep. 5, 2013; U.S. Provisional PatentApplication No. 61/929,947, filed Jan. 21, 2014; and these patentapplications are incorporated herein by reference.

FIELD

Embodiments described herein concern devices and methods that assist gasexchange and stabilize lung volume in patients of all ages withbreathing problems.

BACKGROUND

Patients who have breathing difficulties are conventionally providedbreathing assistance using mechanical ventilators. These devices aregenerally expensive and out of reach of a large portion of thepopulation, particularly in economically disadvantaged countries. Thesedevices also require substantial training and expertise to operate andmaintain. Further, these devices do not provide the user the ability toset and vary upper limit of safe positive pressure that is patientspecific and commensurate with the peak inspiratory pressure levels setduring ventilation in an easy and less expensive way.

In recent years, there has been increasing interest in the developmentof breathing assistance devices that are less expensive. U.S. Pat. No.8,499,759 discloses the use of a two-way valve in a pressure regulatingbreathing assistance apparatus wherein the valve is placed intermediatetwo pressure control conduits that are submerged at varying lengths in asingle container containing a fluid. In such apparatus, depending on thesize of the valve, back pressure is generated whereby the pressure ofgas at a patient interface may be higher than the pressure set using oneof the control conduits, but not the other. This back pressure, if notcorrectly accounted for, has important treatment and safety implicationsif the device is used on a patient. Further, such apparatus require acontainer containing a fluid. The use of a container containing fluidmay not be practical in certain conditions, e.g., when the patient is ina location where fluid is not readily available or fluid shakes andspills because of motion during transport of patients.

There is a significant need to provide a respiratory assistanceapparatus that is easy and less expensive to make, operate and maintain,and has high-positive-pressure safety feature that is simple, reliableand easily adjustable relative to the desired patient-specificinspiratory pressure level.

SUMMARY OF THE INVENTION

It is generally known in the medical profession that stabilization oflung volumes and improvement in gas exchange in patients receivingventilation assistance could be achieved through appropriate settingsand control of the positive pressures generated, amplitude and frequencyof oscillating positive pressure in the ventilator. Embodimentsdescribed herein provide the user a device and method to set peakinspiratory pressure, positive end-expiratory pressure, breaths perminute, inspiratory time, and further allows the user to set the upperlimit of positive pressure that is specific for a patient to reduce thelikelihood of damage to the lungs. Additionally, the embodimentsdescribed herein maintain a patient's mean airway pressure at controlledlevels. Device parameters such as the values of pressures for inhalationand exhalation are adjustable. These embodiments also have features thatallow a user to select and modulate breaths per minute, inspiratorytime, and the ratio of inspiratory to expiratory time. The embodimentsdescribed herein are useful to adults, children and newborn babies.Further, the embodiments can be used during transport of patients, andmay be used in facilities that do not have access to mechanicalventilators.

In one embodiment, a ventilator system is provided having a pressurizedgas supply, two pressure-relief valves, and a primary duct with twoends—the proximal end and the distal end. The proximal end is connectedto the pressurized gas supply. The primary duct is adapted forconnection to a patient interface between the proximal and distal ends.A peak inspiratory pressure control duct is connected to the distal endand a first pressure-relief valve is connected to the peak inspiratorypressure control duct. A positive end-expiratory pressure control ductis also connected to the distal end of the primary duct and a secondpressure-relief valve is connected to the positive end-expiratorypressure control duct. A two-port valve, also known as a two-way valve,is connected in between the inspiratory pressure control duct and thepositive end-expiratory pressure control duct wherein the rate ofopening and closing of the valve can be controlled. In addition, atleast one safety duct is connected to the primary duct near the proximalend and is connected to a third pressure-relief valve. The value ofpressure at which pressure will be relieved using the pressure-reliefvalve connected to the at least one safety duct is controlled by theuser. In some embodiments, pressure-relief valves are adjustable andhave simple markings, for example in cm of water, to help the user sethigh pressure (peak inspiratory pressure), low pressure (positiveend-expiratory pressure), and high-pressure limit (Pop-Off). In otherembodiments, a pressure-relief valve is adjusted by rotating a knobconnected to the valve or by pressing buttons that send signal to thepressure-relief valve to deliver high and low pressures. In yet anotherembodiment, the pressure-relief valve is adjusted using a signal from aprogrammable controller. In certain embodiments, as a safety feature,the default position of the ventilator system is to deliver the lowerpressure at all times as CPAP when the ventilator system is connected tothe patient.

In another embodiment, a pressure-relief valve is connected to the PIPcontrol duct and the PEEP control duct is immersed in a liquid columninside a container. In yet another embodiment, a pressure-relief valveis connected to the PEEP control duct and the PIP control duct isimmersed in a liquid column inside a container. In some embodiments,two-way or three-way valve allows the user to set breathing rates from4-60 per minute, known as conventional mechanical breaths. In otherembodiments, the breathing rates are in the range of 60-900 per minute,known as high frequency range. In yet another embodiment, a controllerallows the user to control inspiratory to expiratory ratios or have itfixed as percent of cycle time to maintain a desired inspiration time toexpiration time ratio, when the cycle frequencies are adjusted. Valvesused in the embodiments include without limitation solenoid valves,pneumatic valves and solar powered valves.

In another embodiment, a ventilator system is provided having apressurized gas supply, two pressure-relief valves, and a primary ductwith two ends—the proximal end and the distal end. The proximal end isconnected to the pressurized gas supply. The primary duct is adapted forconnection to a patient interface between the proximal and distal ends.Also provided is a three-port valve (also known as a three-way valve)having one inlet port and two outlet ports. The distal end of theprimary duct is connected to the inlet port of the valve. The firstoutlet port of the valve is connected to a peak inspiratory pressurecontrol duct that is connected to a first pressure-relief valve. Thesecond outlet port of the valve is connected to a positiveend-expiratory pressure control duct that is connected to a secondpressure-relief valve. In operation, the valve alternatively connectsthe inlet port to the first outlet port and the second outlet port,i.e., the gas entering the inlet port passes through the first outletport for a period of time and then the gas entering the inlet portpasses through the second outlet port for another period of time,completing a cycle of passage of gas through the first outlet port andthe second outlet port. The cycle then repeats. A controllercommunicably connected to the valve controls the number of cycles perunit time, for example, number of cycles per minute. In addition, atleast one safety duct is connected to the primary duct near the proximalend and is connected to a third pressure-relief valve that is set at avalue greater than the value set for the pressure-relief valve connectedto the peak inspiratory pressure control duct.

In another embodiment, the pressure-relief valves are mechanical and thelevel at which pressure will be relieved is set by a mechanical device,e.g., a knob that is connected to the valve. In another embodiment, thepressure-relief valves are electro-mechanical and the level at whichpressure will be relieved is set by a controller that sends a signal tothe pressure-relief valve. In yet another embodiment, thepressure-relief valve is a pneumatic valve or a solenoid valve. In oneembodiment, the pressure relief valve is a variable pressure-reliefvalve in which the value of pressure at which a pressure relief occurscan be varied.

In some embodiments, the peak inspiratory pressure control duct and theend-expiratory pressure control duct are substantially circular havingan inside diameter of between about 0.5 to 2 cm and the pressure-reliefvalves are adjustable in the pressure range of about 0-50 cm H2O.

DESCRIPTION OF THE DRAWINGS

FIG. 1 depicts a ventilator system utilizing a peak inspiratory pressurecontrol duct connected to a first pressure-relief valve; a positiveend-expiratory pressure control duct connected to a secondpressure-relief valve; and one two-port valve located in-between thepeak inspiratory pressure control duct and the positive end-expiratorypressure control duct. Based on the durations of valve open and shuttimes, low as well high frequency breathing support can be delivered atfixed or variable ratio of inspiratory to expiratory time.

FIG. 2 depicts a ventilator system utilizing a peak inspiratory pressurecontrol duct connected to a first pressure-relief valve; a positiveend-expiratory pressure control duct immersed in a fluid in a container;one two-port valve located in-between the peak inspiratory pressurecontrol duct and the positive end-expiratory pressure control duct; andone high pressure safety duct connected to a second pressure-reliefvalve.

FIG. 3 depicts a ventilator system as shown in FIG. 2 without the highpressure safety duct and with an angled portion added to the positiveend-expiratory pressure control duct.

FIG. 4 depicts a ventilator system as shown in FIG. 1 with an additionof one high pressure safety duct connected to a third pressure-reliefvalve.

FIG. 5 depicts a ventilator system utilizing a peak inspiratory pressurecontrol duct connected to a first pressure-relief valve; a positiveend-expiratory pressure control duct connected to a secondpressure-relief valve; one three-port valve connected to the peakinspiratory pressure control duct, the positive end-expiratory pressurecontrol duct and a primary duct.

FIG. 6 depicts a ventilator system utilizing a peak inspiratory pressurecontrol duct connected to a first pressure-relief valve; a positiveend-expiratory pressure control duct immersed in a fluid in a container;one three-port valve connected to the peak inspiratory pressure controlduct, the positive end-expiratory pressure control duct and a primaryduct; one high pressure safety duct connected to a secondpressure-relief valve.

FIG. 7 depicts a ventilator system as shown in FIG. 6 without the highpressure safety duct and with an angled portion added to the positiveend-expiratory pressure control duct.

FIG. 8 depicts a ventilator system as shown in FIG. 5 with an additionof one high pressure safety duct connected to a third pressure-reliefvalve.

FIG. 9 depicts a spring-loaded pressure-relief valve.

FIG. 10 depicts a manually adjusted pressure-relief valve.

FIG. 11 depicts a ventilator system utilizing a peak inspiratorypressure control duct connected to a first pressure-relief valve; apositive end-expiratory pressure control duct connected to a secondpressure-relief valve; one three-port valve connected to the peakinspiratory pressure control duct, the positive end-expiratory pressurecontrol duct and a primary duct; and a controller communicably connectedto the three-port valve, the first pressure-relief valve, and the secondpressure-relief valve.

FIG. 12 depicts a ventilator system utilizing a peak inspiratorypressure control duct connected to a first pressure-relief valve; apositive end-expiratory pressure control duct connected to a secondpressure-relief valve; one two-port valve located on the positiveend-expiratory pressure control duct; one two-port valve located on thepeak inspiratory pressure control duct; a controller communicablyconnected to both the two-port valves, and also communicably connectedto the first pressure-relief valve and the second pressure-relief valve.

DETAILED DESCRIPTION

Embodiments described herein provide the user a device and method to sethigh and low pressures, oscillations, amplitude and frequency andfurther allows the user to set the upper limit of positive pressure thatis specific for a patient to reduce the likelihood of damage to thelungs. Device parameters such as pressure value at which thepressure-relief valve will activate, level of fluid in a container,length of the duct immersed in the fluid in the container can be variedto control the pressures. In another embodiment, a system may not use aduct immersed in a fluid in a container for pressure control, and allpressures are controlled by pressure-relief valves. In some embodiments,pressure regulators or pressure control valves may be used instead of apressure-relief valve. For example, a diaphragm pressure regulator maybe used instead of a pressure-relief valve. In the present description,a reference to a pressure-relief valve also refers to any valve such asa pressure regulator that can control pressure upstream of the valve.

The embodiments described herein also have features that allow the userto select and modulate breaths per minute, inspiratory time, and theratio of inspiratory to expiratory time. The embodiments are useful forpatients of all ages including adults, children and newborn babies.Further, the embodiments can be used during transport of patients of allages and in facilities that do not have access to mechanicalventilators. In operation, pressurized gas is released from the gassupply into the primary duct of an embodiment described herein, and thegas is delivered to a patient

FIG. 1 illustrates a patient ventilation system 100 having a pressurizedgas supply 102, two pressure-relief valves 118 and 122, and a primaryduct 108 with two ends—the proximal end 110 and the distal end 112. Theproximal end 110 is connected to the pressurized gas supply 102. Theduct 108 is adapted for connection to a patient interface 114 betweenthe proximal end 110 and distal end 112. At the distal end 112, at leastone peak inspiratory pressure (PIP) control duct 116 is connected. Theproximal end of the PIP control duct 116 is connected to the distal end112 of the primary duct 108. The distal end of the PIP control duct 116is connected to a pressure-relief valve 118. At least one positiveend-expiratory pressure (PEEP) control duct 120 is also connected to thedistal end 112 of the primary duct 108. The proximal end of the PEEPcontrol duct 120 is connected to the distal end 112 of the primary duct108. The distal end of the PEEP control duct 120 is connected to apressure-relief valve 122. A two-port valve 124 is connected in betweenthe inspiratory pressure control duct and the positive end-expiratorypressure control duct. The valve 124 cycles from open to shut positionand back to open position, and the rate of cycling of the valve can becontrolled by a controller (not shown) communicably connected to thevalve. The failure mode of the valve 124 is the open position wherebythe gas flow is directed to the positive end expiratory pressure (PEEP)control duct 120 and the pressure at the patient interface 114 ismaintained at the lower or baseline level.

In some embodiments of the PIP and PEEP control ducts, the diameters ofthe ducts are about 0.5 cm to 2 cm. In other embodiments, more than onePIP control duct and more than one PEEP control duct may be used. In yetother embodiments, the PIP and PEEP control ducts may each havesubstantially similar lengths and diameters or different lengths anddiameters. The lengths and cross-sectional shapes of the primary duct,the PIP control duct, and the PEEP control duct are preferably short andsubstantially circular or slightly oval in shape. However, any or all ofthe ducts can have any length or cross-sectional shape including but notlimited to square, rectangular, triangular etc., without departing fromthe spirit of the present disclosure.

A gas supply provides pressurized medical grade gas to the ventilatorsystem including to the primary duct, patient duct, PIP control duct andPEEP control duct. Gas delivered by the gas supply may compriseatmospheric gases or any combination, mixture, or blend of suitablegases, including but not limited to atmospheric air, oxygen, nitrogen,helium, or combinations thereof. The gas supply may comprise a gascompressor, a container of pressurized gases, a substantially portablecontainer of pre-pressurized gases, a gas-line hookup (such as found ina hospital) or any other suitable supply of pressurized gas, orcombinations thereof. The gas supply is preferably controlled orconfigured to have a variable gas flow rates that can be controlled byuser and adjusted according to the individual requirements of eachpatient. The patient ventilation system or gas supply may also includeone or more flow control devices (not shown) including but not limitedto a mechanical valve, an electronically controlled mechanical valve, arotameter, a pressure regulator, a flow transducer, or combinationsthereof. Gas flow rates, which are commonly used in the art, typicallyrange from about 2 liters/minute (L/min) to about 15 L/min. However,these embodiments allow any flow rates of gas set by the user. Forexample, larger patients may require larger gas flows. Increasing theflow rates could result in the delivery of higher pressures; however, bysetting the high-pressure blow-out level of the safety duct to a safelevel, one can avoid inadvertent delivery of excessively high pressuresto the patient.

A Heat and Moisture Exchanger (not shown) can also be included in thepatient ventilation system to control the temperature and humidity ofgas delivered to the patient interface. Continuous flow of gas in thedelivery duct also prevents the patient from re-breathing gases exhaledfrom the lungs.

Referring to FIG. 1, the patient interface 114 can be invasive ornon-invasive, including but not limited to face or nasal masks, nasalprongs, nasal cannula, short tube(s) placed in the nasal ornaso-paharynx, endotracheal tubes, tracheostomy tubes, or combinationsthereof. The two-port valve 124 may comprise a mechanical orelectromechanical valve. The two-port valve 124 may be electronicallycontrolled or mechanically controlled such that the user is able to setthe ventilation rate and inspiratory time or the ratio of inspiratory toexpiratory time. The two-port valve 124 is preferably “normally open”such that in the event of failure the valve would remain open and thepatient would be subjected to the lower or baseline pressure. When thetwo-port valve 124 is open, gases flow through PEEP control duct 120 toPEEP pressure-relief valve 122, which is set to relieve pressure at alevel lower than the set level of PIP pressure-relief valve 118 therebycontrolling the positive end expiratory pressure in the circuit. Whenthe two-port valve 124 is closed, gas in the pressurized circuit flowsthrough PIP control duct 116 to PIP pressure-relief valve 118, which isset to relieve pressure at a level higher than the set level of PEEPpressure-relief valve 122, thereby raising the pressure to peakinspiratory pressure and delivering a “mandatory breath” to the patient.The valve 124 can then be opened again to allow the patient to exhale,and the process may be repeated. In this manner, a patient can receivepeak inspiratory pressure and positive end expiratory pressure (Bi-PAPventilation) or intermittent positive pressure ventilation (IPPV). Insome embodiments, any number of valves, PIP control ducts and PEEPcontrol ducts can be used to provide different levels of high and lowpressures. In another embodiment, the PIP and PEEP pressure-reliefvalves may be directly and/or logically connected to a controller (notshown) associated with the system. In one embodiment, each of a movementof PIP valve, PEEP valve, and the two-way valve is controlled bycontroller. In one embodiment, controller contains machine-readableprogram instructions as a form of non-transitory tangible media.

FIG. 2 illustrates a ventilator system similar to FIG. 1, the differencebeing the PEEP safety relief valve 122 of FIG. 1 is replaced with acontainer 206 having a fluid 222. In addition, the ventilator system ofFIG. 2 has at least one safety duct 230. The safety duct 230 isconnected to the primary duct 208 near the proximal end 210 of theprimary duct 208. The safety duct 230 is connected to a pressure-reliefvalve 204 which is set at a level of pressure greater than the level ofpressure set in the PIP pressure-relief valve 218. The safety ductallows setting the limit of a safe pressure relative to the set PIPpressure. For example, in some embodiments the safety pressure-reliefvalve 204 is set to relieve pressure at a level that is 5 cm of waterhigher than the set level of pressure in the PIP pressure-relief valve218, if the user wants the maximum pressure that the lungs may besubjected to be not greater than the set PIP pressure by 5 cm of water.

The fluid 222 may comprise any number of suitable fluids or liquidsexhibiting a wide range of densities, masses and viscosities includingbut not limited to water, or water with added vinegar to reduce thelikelihood of bacterial contamination of the water. In certainembodiments, the peak inspiratory pressure control duct and the positiveend-expiratory pressure control duct are substantially circular havingan inside diameter of between about 0.5-2 cm. The immersed length insidethe container is in the range of about 2-50 cm. The immersed verticallength of PEEP control duct can be measured as the vertical distancefrom the fluid surface to the distal ends of the ducts. In allembodiments, the immersed vertical length of the PEEP control duct canbe adjusted to any value by adding or removing fluid to adjust fluidlevel, by sliding the ducts up and down to adjust the duct location, ordoing both. The set level of PEEP pressure corresponds to the immersedvertical length of the PEEP control duct.

FIG. 3 illustrates a patient ventilator system similar to thatillustrated in FIG. 2 utilizing a PEEP control duct 320 in the container306, except that the system in FIG. 3 does not have a safety duct and asafety valve as shown in FIG. 2. The duct 320 is immersed in fluid andconfigured to modulate airway pressures in a patient receiving Bi-PAP orIPPV. The embodiment illustrated in FIG. 3 further comprises an angledsection 334 connected to the distal ends of the PEEP control duct. Theangle of angled section may be altered between 0 and 180 degrees to thevertical to control the amplitude and frequency of airway pressureoscillations that are superimposed on top of the airway pressure waveform for the exhalation cycle. In some embodiments, the angled arm ofthe angled section has length of between 2 cm and 10 cm. In otherembodiments, more than two angled sections may be used. In oneembodiment, the angles of the two or more angled sections may besubstantially similar. In other embodiments, the angles of the two ormore angled sections may be different. In one embodiment, the diameterof the angled section is the same as the diameter of the PEEP controlduct. In another embodiment, the diameter of the angled section isdifferent from the diameter of the PEEP control duct. The immersedvertical length of PEEP control duct can be measured as the verticaldistance from the fluid surface to the elbow of the angled section.

FIG. 4 illustrates a ventilator system similar to FIG. 1, but has inaddition, at least one safety duct 430. The safety duct 430 is connectedto the primary duct 408 near the proximal end 410 of the primary duct408. The safety duct 430 is connected to a pressure-relief valve 404which is set at a level of pressure greater than the level of pressureset in the PIP pressure-relief valve 418. The safety duct allows settingthe limit of a safe pressure relative to the set PIP pressure.

In another embodiment, the PEEP pressure-relief valve 422 may be absentand the gas coming out of the PEEP duct 420 is released directly to theatmosphere without passing through a PEEP pressure-relief valve. ThePEEP pressure of the ventilator system then corresponds to theback-pressure of the two-port valve 424. The PEEP pressure in thisembodiment would be equal to the back pressure of the valve 424 at theflow rate of gas in the ventilator system.

FIG. 5 illustrates a patient ventilator system 500 having a pressurizedgas supply 502, two pressure-relief valves 518 and 522, and a primaryduct 508 with two ends—proximal end 510 and distal end 512. The proximalend 510 is connected to the pressurized gas supply 502. The primary duct508 is adapted for connection to a patient interface 514 between theproximal end 510 and distal end 512. A three-port (also known asthree-way) valve 525 is provided with one inlet port and two outletports. The distal end 512 is connected to the inlet port of thethree-port valve 525. The first outlet port of the valve 525 isconnected to at least one peak inspiratory pressure (PIP) control duct516. A proximal end of the PIP control duct 516 is connected to thefirst outlet port of the valve 525 and the distal end of the PIP controlduct 516 is connected to a PIP pressure-relief valve 518. The secondoutlet port of the valve 525 is connected to at least one positiveend-expiratory pressure (PEEP) control duct 520. The proximal end of thePEEP control duct 520 is connected to the second outlet port of thevalve 525. The distal end of the PEEP control duct 520 is connected to aPEEP pressure-relief valve 522.

The valve 525 cycles between the first outlet port and the second outletport thereby continuously switching the flow of gas from the inlet portto the first outlet port and the inlet port to the second outlet port.Each cycle corresponds to one breath. In operation, when the gas flowsfrom the inlet port to the first outlet port of valve 525, gas flowsthrough PIP control duct 516 to the PIP pressure-relief valve 518, whichis set at a level of pressure higher than the level of pressure set inthe PEEP pressure-relief valve 522, thereby controlling the PIP in thecircuit. When the gas flows from the inlet port to the second outletport of valve 525, gas in the pressurized circuit flows through PEEPcontrol duct 520 to the PEEP pressure-relief valve 522, which is set ata level of pressure lower than the level of pressure set in the PIPpressure-relief valve 518, thereby lowering the pressure to PEEP andallowing the patient to exhale. The valve 525 can then cycle back to thefirst outlet port to allow the patient to receive PIP, and the cycle maybe repeated. In this manner, a patient can receive peak inspiratorypressure and positive end expiratory pressure (Bi-PAP ventilation) orintermittent positive pressure ventilation (IPPV).

In one embodiment, rate of cycling (measured in cycles per minute) ofthe valve 525 is controlled using a controller (not shown) communicablyconnected to the valve. In another embodiment, controller allows user toset time T1 (Inspiratory Time) during which gas flows from the inletport to the first outlet port and time T2 (Expiratory Time) during whichgas flows from the inlet port to the second outlet port. In oneembodiment, T1 is set as time in seconds. In another embodiment, T1 orT2 can be set as a fraction of cycle time or as a ratio of T1 and T2such that the sum of T1 and T2 equals time of one cycle. Because the PIPcontrol duct is connected to the first outlet port and the PEEP controlduct is connected to the second outlet port, T1 is inspiratory time andT2 is expiratory time of a cycle or breath. In one embodiment, theexpiratory time T2 is set to be greater than inspiratory time T1, andthe ratio T2/T1 is greater than 1. The ratio of inspiratory time andexpiratory time may be depicted as T1:T2 and the ratio shown as 1:Nwhere, in one embodiment, N is a number greater than 1. In anotherembodiment, the controller does not allow the value of N to be lessthan 1. In another embodiment, breaths per minute (bpm) and inspiratorytime (T1) in seconds are set by the user, and the controller calculatesexpiratory time (T2) in seconds using the formula T2=(60/bpm)−T1. In yetanother embodiment, if the calculated expiratory time (T2) in seconds isless than the inspiratory time (T1) in seconds set by the user, thecontroller sets T1=T2=30/bpm. In another embodiment, controller allowsthe user to control the ratio of inspiratory time T1 to expiratory timeT2 or have T1 fixed as percent of cycle time to maintain a desiredinspiration time to expiration time ratio. For example, if T1 is set as33% of cycle time, then T2 will be 67% of cycle time, giving T1:T2 ratioof 1:2. In another embodiment, the controller is integrated with thevalve, with the control logic embedded in the valve. In one embodiment,the failure mode of the valve 525 is the open position to the secondoutlet port whereby the gas flow is directed to the PEEP control duct520 and the pressure in the ventilator system is maintained at thebaseline, i.e. lower level. In another embodiment, if the controllersets the cycling rate of the valve 525 as zero, the valve remains in theopen position to the second outlet port whereby the gas flow is directedto the PEEP control duct 520 and the pressure in the ventilator systemis maintained at the baseline i.e. lower level. In another embodiment,if power to the valve 525 is shut off, the valve remains in the openposition to the second outlet port whereby the gas flow is directed tothe PEEP control duct 520 and the pressure in the ventilator system ismaintained at the baseline i.e. lower level. Thus the apparatus can beconverted from Bi-PAP ventilation to CPAP by simply shutting off powerto the valve or setting cycling rate of the valve to zero.

In one embodiment, the pressure-relief valves 518 and 522 aremechanical. The level of pressure at which the pressure relief willoccur is set manually using a knob or a dial. In another embodiment, thepressure-relief valves are electro-mechanical. The level of pressure atwhich the pressure relief will occur is set using a controller.Depending on the level set in the controller at which the pressurerelief is to occur, the controller sends a signal to valve whereby thevalve adjusts the valve position and opening to the required level ofpressure relief.

FIG. 6 illustrates a ventilator system similar to FIG. 5, the differencebeing the PEEP pressure-relief valve 522 of FIG. 5 is replaced with acontainer 606 having a fluid 622. In addition, the ventilator system ofFIG. 6 has at least one safety duct 630. The safety duct 630 isconnected to the primary duct 608 near the proximal end 610 of theprimary duct 608. The safety duct 630 is connected to a pressure-reliefvalve 604 which is set at a level of pressure greater than the level ofpressure set in the PIP pressure-relief valve 618. The safety ductallows setting the limit of a safe pressure relative to the set PIPpressure. For example, in some embodiments the safety pressure-reliefvalve 604 is set to relieve pressure at a level that is 5 cm of waterhigher than the set level of pressure in the PIP pressure-relief valve618, if the user wants the maximum pressure that the lungs may besubjected to be not greater than the set PIP pressure by 5 cm of water.

The fluid 622 may comprise any number of suitable fluids or liquidsexhibiting a wide range of densities, masses and viscosities includingbut not limited to water, or water with added vinegar to reduce thelikelihood of bacterial contamination of the water. In certainembodiments, the peak inspiratory pressure control duct and theend-expiratory pressure control duct are substantially circular havingan inside diameter of between about 0.5-2 cm. The immersed length insidethe container is in the range of about 2-50 cm. The immersed verticallength of PEEP control duct can be measured as the vertical distancefrom the fluid surface to the distal ends of the ducts. In allembodiments, the immersed vertical length of the PEEP control duct canbe adjusted to any value by adding or removing fluid to adjust fluidlevel, by sliding the ducts up and down to adjust the duct location, ordoing both. The set level of PEEP pressure corresponds to the immersedvertical length of the PEEP control duct.

FIG. 7 illustrates a ventilator system similar to that illustrated inFIG. 6 utilizing a PEEP control duct 720 in the container 706, exceptthat the system in FIG. 7 does not have a safety duct and a safety valveas shown in FIG. 6. The duct 720 is immersed in fluid and configured tomodulate airway pressures in a patient receiving Bi-PAP or IPPV. Theembodiment illustrated in FIG. 7 further comprises an angled section 734connected to the distal end of the PEEP control duct. The angle ofangled section may be altered between 0 and 180 degrees to the verticalto modify the amplitude and frequency of airway pressure oscillationsthat are superimposed on top of the airway pressure wave form for boththe exhalation cycle. In some embodiments, the angled arm of the angledsection has length of between 2 cm and 10 cm. In some embodiments, morethan two angled sections may be used. In other embodiments, the anglesof the two or more angled sections may be substantially similar. Instill other embodiments, the angles of the two or more angled sectionsmay be different.

FIG. 8 illustrates a ventilator system similar to FIG. 5, but has inaddition, at least one safety duct 830. The safety duct 830 is connectedto the primary duct 808 near the proximal end 810 of the primary duct808. The safety duct 830 is connected to a pressure-relief valve 804which is set at a level of pressure greater than the level of pressureset in the PIP pressure-relief valve 818. The safety duct allows settingthe limit of a safe pressure relative to the set PIP pressure.

In another embodiment, the PEEP pressure-relief valve 822 is absent andthe gas coming out of the PEEP duct 820 is released directly to theatmosphere without passing through a PEEP pressure-relief valve. ThePEEP pressure of the ventilator system then corresponds to theback-pressure of the three-port valve 825. The PEEP pressure in thisembodiment would be equal to the back pressure of the valve 825 at theflow rate of gas in the ventilator system.

In addition to the safety duct illustrated in FIGS. 2, 4, 6 and 8, someembodiments can include additional safety features (not shown) such as ahigh pressure “pop-off” or “pop-open” safety valve to protect thepatient from receiving airway pressures greater than a pre-determinedthreshold to reduce the likelihood of high pressures reaching thepatient in the unlikely event that the patient circuit is occludedbetween the patient and the gas exiting the system through the fluidcontainer. The pop-off valve provides a second level of protection whenthe safety duct such as duct 230 in FIG. 2 is present in the ventilatorsystem. The pressure level setting of pop-off valve will be generallyhigher than the blow-out pressure setting of the safety duct. Notehowever that pop-off safety valve is generally pre-set to certain valuesand does not provide user the flexibility provided by the safety duct,which allows setting the limit of safe pressure relative to the set PIPpressure.

FIG. 9 shows an embodiment of a pressure-relief valve. Thepressure-relief valve 900 can be set to control pressure of gas upstreamof the valve. A knob 901 is rotated manually clockwise orcounter-clockwise to set the pressure at which the pressure relief willoccur. The relief pressure is set by rotating the knob to appropriatepressure marking on the body of the valve 903. In another embodiment,the pressure markings are on a circular dial around the top perimeter ofthe knob. The gas enters the valve 900 at the inlet port 905 and exitsthe valve at outlet ports 906. A float 907 is placed in a cavity 909inside the body of the valve 903 with the conical end of the floataligned with the conical end of the cavity 909. A spring 910 is thenplaced in the cavity 909 on top of the float and in between the floatand the knob 901. In one embodiment, when the knob 901 is rotatedclockwise, the spring 910 compresses on the float 907 thereby pressingit against the entrance of the valve. Depending on the pressure of thegas entering the valve 900, the spring is pushed back, thereby releasingthe gas through outlet ports 906 and maintaining a gas pressure in thesystem upstream of the valve. The valve can be made of plastic or metalssuch as brass and steel. In other embodiments of the ventilator system,a diaphragm pressure regulator may be used instead of the springpressure-relief valve.

FIG. 10 shows an embodiment of pressure-relief valve similar to thepressure-relief valve in FIG. 9, except that the valve in FIG. 10 doesnot have a spring. In FIG. 10, the float 917 is directly connected tothe knob 911 and is an integral part of the knob. When the knob 911 isscrewed into the body 913, the float 917 takes a position inside thecavity 919 of the valve. The location of the float 917 inside the cavity919 depends on the number of times the knob is rotated on threads 922.Depending on the location of the float 917, there remains a gap betweenthe float 917 and the cone 924 inside the cavity 919. This gap offers aresistance to the gas entering the valve at the inlet port 915. Theupstream pressure of the gas can be set by adjusting the size of the gapwhich in turn is done by rotating the knob 911. In another embodiment,the pressure-relief valve may be directly and/or logically connected toa controller associated with the system, and the movement ofpressure-relief valve is controlled by the controller. In oneembodiment, controller contains machine-readable program instructions asa form of non-transitory tangible media.

Some embodiments can include a low-pressure “pop-open” or one-way valve(not shown) to protect the patient from receiving airway pressures lowerthan a pre-determined threshold, for example sub-atmospheric pressures.In this manner, the one-way valve can help prevent a lung fromcollapsing, help prevent the patient from inhaling fluid, and helpprevent the patient from re-breathing exhaled gases. Fresh gas ofcontrolled concentration (not shown) can also be supplied to the one-wayvalve.

FIG. 11 illustrates a patient ventilator system having a pressurized gassupply 502, two pressure-relief valves 505 and 523, and a primary duct508 with two ends—proximal end 510 and distal end 512. The proximal end510 is connected to the pressurized gas supply 502. The primary duct 508is adapted for connection to a patient interface 514 between theproximal end 510 and distal end 512. A three-port (also known asthree-way) valve 525 is provided with one inlet port and two outletports. The distal end 512 is connected to the inlet port of thethree-port valve 525. The first outlet port of the valve 525 isconnected to at least one peak inspiratory pressure (PIP) control duct517. A proximal end of the PIP control duct 517 is connected to thefirst outlet port of the valve 525 and the distal end of the PIP controlduct 517 is connected to a PIP pressure-relief valve 505. The secondoutlet port of the valve 525 is connected to at least one positiveend-expiratory pressure (PEEP) control duct 521. The proximal end of thePEEP control duct 521 is connected to the second outlet port of thevalve 525. The distal end of the PEEP control duct 521 is connected to apressure-relief valve 523.

The valve 525 cycles between the first outlet port and the second outletport thereby continuously switching the flow of gas from the inlet portto the first outlet port and the inlet port to the second outlet port.Each cycle corresponds to one breath. In operation, when the gas flowsfrom the inlet port to the first outlet port of valve 525, gas flowsthrough PIP control duct 517 to the PIP pressure-relief valve 505, whichis set at a level of pressure higher than the level of pressure set inthe PEEP pressure-relief valve 523, thereby controlling the PIP in thecircuit. When the gas flows from the inlet port to the second outletport of valve 525, gas in the pressurized circuit flows through PEEPcontrol duct 521 to the PEEP pressure-relief valve 523, which is set ata level of pressure lower than the level of pressure set in the PIPpressure-relief valve 505, thereby lowering the pressure to PEEP andallowing the patient to exhale. The valve 525 can then cycle back to thefirst outlet port to allow the patient to receive PIP, and the cycle maybe repeated. In this manner, a patient can receive peak inspiratorypressure and positive end expiratory pressure (Bi-PAP ventilation) orintermittent positive pressure ventilation (IPPV).

In one embodiment, rate of cycling (measured in cycles per minute) ofthe valve 525 is controlled using a controller 515 communicablyconnected to the valve. In another embodiment, controller 515 allowsuser to set time T1 (Inspiratory Time) during which gas flows from theinlet port to the first outlet port and time T2 (Expiratory Time) duringwhich gas flows from the inlet port to the second outlet port. In oneembodiment, T1 is set as time in seconds. In another embodiment, T1 orT2 can be set as a fraction of cycle time or as a ratio of T1 and T2such that the sum of T1 and T2 equals time of one cycle. Because the PIPcontrol duct is connected to the first outlet port and the PEEP controlduct is connected to the second outlet port, T1 is inspiratory time andT2 is expiratory time of a cycle or breath. In one embodiment, theexpiratory time T2 is set to be greater than inspiratory time T1, andthe ratio T2/T1 is greater than 1. The ratio of inspiratory time andexpiratory time may be depicted as T1:T2 and the ratio shown as 1:Nwhere, in one embodiment, N is a number greater than 1. In anotherembodiment, the controller 515 does not allow the value of N to be lessthan 1. In another embodiment, breaths per minute (bpm) and inspiratorytime (T1) in seconds are set by the user, and the controller 515calculates expiratory time (T2) in seconds using the formulaT2=(60/bpm)−T1. In yet another embodiment, if the calculated expiratorytime (T2) in seconds is less than the inspiratory time (T1) in secondsset by the user, the controller 515 sets T1=T2=30/bpm. In anotherembodiment, controller 515 allows the user to control the ratio ofinspiratory time T1 to expiratory time T2 or have T1 fixed as percent ofcycle time to maintain a desired inspiration time to expiration timeratio. For example, if T1 is set as 33% of cycle time, then T2 will be67% of cycle time, giving T1:T2 ratio of 1:2. In another embodiment, thecontroller 515 is integrated with the valve, with the control logicembedded in the valve.

In one embodiment, the failure mode of the valve 525 is the openposition to the second outlet port whereby the gas flow is directed tothe PEEP control duct 521 and the pressure in the ventilator system ismaintained at the baseline, i.e. lower level. In another embodiment, ifthe controller 515 sets the cycling rate of the valve 525 as zero, thevalve remains in the open position to the second outlet port whereby thegas flow is directed to the PEEP control duct 521 and the pressure inthe ventilator system is maintained at the baseline i.e. lower level. Inanother embodiment, if power to the valve 525 or the controller 515 isshut off, the valve remains in the open position to the second outletport whereby the gas flow is directed to the PEEP control duct 521 andthe pressure in the ventilator system is maintained at the baseline i.e.lower level. Thus the apparatus can be converted from Bi-PAP ventilationto CPAP by simply shutting off power to the valve or setting cyclingrate of the valve to zero. In one embodiment, the controller 515 isconnected to the three-port valve 525 with wires, and the controller 515communicates with the three-port valve 525 through the wires. In anotherembodiment, the controller 515 communicates with the three-port valve525 wirelessly and communication between the three-port valve 525 andthe controller 515 can be achieved using any of the generally knownwireless protocols. In another embodiment, the PIP pressure-relief valve505 and the PEEP pressure-relief valve 523 may be directly and/orlogically connected to controller 515 associated with the system. In oneembodiment, each of a movement of PIP valve 505, PEEP valve 523 and thethree-way valve 525 is controlled by controller 515. In one embodiment,controller contains machine-readable program instructions as a form ofnon-transitory tangible media. In another embodiment, controller may bedirectly and/or logically connected to a monitoring device that monitorsthe vitals such as blood oxygen level and blood pressure of a patient.In yet another embodiment, controller may communicate with an iDevicesuch as iPad or iPhone, and the settings of the controller can bemonitored and adjusted using the iDevice.

In one embodiment, the pressure-relief valves 505 and 523 aremechanical. The level of pressure at which the pressure relief willoccur is set manually using a knob or a dial. In another embodiment, thepressure-relief valves are electro-mechanical. The level of pressure atwhich the pressure relief will occur is set using the controller 515.Depending on the level of pressure set in the controller 515 at whichthe pressure relief is to occur, the controller sends a signal to thepressure-relief valve whereby the valve adjusts the position and openingof the valve to the required level of pressure relief. In oneembodiment, the controller 515 is connected to the pressure-reliefvalves 505 and 523 with wires and the controller 515 communicates withthe pressure-relief valves 505 and 523 through the wires. In anotherembodiment, the controller 515 communicates with the pressure-reliefvalves 505 and 523 wirelessly and the communication between thepressure-relief valves and the controller is achieved using any of thegenerally known wireless protocols.

FIG. 12 illustrates a patient ventilation system having a pressurizedgas supply 102, pressure-relief valves 105 and 107, and a primary duct108 with two ends—the proximal end 110 and the distal end 112. Theproximal end 110 is connected to the pressurized gas supply 102. Theduct 108 is adapted for connection to a patient interface 114 betweenthe proximal end 110 and distal end 112. At the distal end 112, at leastone peak inspiratory pressure (PIP) control duct 117 is connected. Theproximal end of the PIP control duct 117 is connected to the distal end112 of the primary duct 108. The distal end of the PIP control duct 117is connected to PIP pressure-relief valve 105. At least one positiveend-expiratory pressure (PEEP) control duct 121 is also connected to thedistal end 112 of the duct. The proximal end of the PEEP control duct121 is connected to the distal end of the primary duct 108. The distalend of the PEEP control duct 121 is connected to the PEEPpressure-relief valve 107. The PIP pressure-relief valve 105 is set torelieve pressure at a level greater than the level of pressure at whichthe PEEP pressure-relief valve 107 is set to relieve the pressure. Atwo-port valve 109 is placed on the PIP control duct 117 and is locatedbetween the PIP control duct 117 and the distal end 112 of the primaryduct. Another two-port valve 125 is placed on the PEEP control duct 121and is located between the PEEP control duct 121 and the distal end 112of the primary duct. The valves 109 and 125 cycle from open to shutposition and back to open position, and the rate of cycling of thevalves can be controlled by a controller 115 communicably connected tothe valves 109 and 125. The valves 109 and 125 are controlled by thecontroller 115 such that when the valve 109 is open, the valve 125 isclosed and when the valve 109 is closed, the valve 125 is open.

In operation, when the two-port valve 125 is open and the two-port valve109 is closed, gases flow through PEEP control duct 121, therebycontrolling the PEEP in the circuit. When the two-port valve 125 isclosed and the two-port valve 109 is open, gases in the pressurizedcircuit flows through PIP control duct 117, thereby raising the pressureto peak inspiratory pressure. The valve 125 can then be opened again andvalve 109 closed to allow the patient to exhale, and the process may berepeated. In this manner, a patient can receive peak inspiratorypressure and positive end expiratory pressure (Bi-PAP ventilation) orintermittent positive pressure ventilation (IPPV).

In one embodiment, the controller 115 is connected to the two-portvalves 109 and 125 using wires and the controller 115 communicates withthe two-port valves 109 and 125 through the wires. In anotherembodiment, the controller 115 is connected to the two-port valves 109and 125 wirelessly and communication between the two-port valves and thecontroller is achieved using any of the generally known wirelessprotocols. In one embodiment, the pressure-relief valves 105 and 107 aremechanical. The level of pressure at which the pressure relief willoccur is set manually using a knob or a dial. In another embodiment, thepressure-relief valves are electro-mechanical. The level of pressure atwhich the pressure relief will occur is set using the controller 115.Depending on the level of pressure set in the controller 115 at whichthe pressure relief is to occur, the controller sends a signal to thepressure-relief valve whereby the valve adjusts the position and openingof the valve to the required level of pressure relief. In oneembodiment, the controller 115 communicates with the pressure-reliefvalves 105 and 107 through wires. In another embodiment, the controller115 communicates with the pressure-relief valves 105 and 107 wirelesslyand the communication between the pressure-relief valves and thecontroller is achieved using any of the generally known wirelessprotocols.

More embodiments concern methods of using one or more of theaforementioned combinations to assist the breathing of a subject (e.g.,an adult, child, infant human being or another mammal). By someapproaches, a subject having breathing problems is identified orselected and said subject is connected to one or more of the devicesdescribed herein. In some embodiments the subject is attached to thedevice by nasal prongs and in other embodiments, the subject is attachedto the device by face or nasal masks, tube(s) placed in the nasopharynx,endotracheal tubes, tracheostomy tubes, or combinations thereof. Oncethe subject and device are connected, gas flow is initiated. Preferablegas flows for infants are about 1 to 10 L/min, whereas adults mayrequire gas flows of about 1 to 30 L/min and large mammals may require 1to 100 L/min or more. Optionally, the frequency, amplitude of cyclingpressure, or volume of gas delivered is monitored so as to adjust thebreathing assistance for the particular subject. In some embodiments, apatient in need of breathing assistance is selected or identified and abreathing assistance device, as described herein, is selected oridentified according to a subject's age, size, or therapeutic need.

Some embodiments include a method for providing continuous positiveairway pressure with oscillating positive end-expiratory pressure to asubject by providing any of the devices or apparatuses described herein,releasing gas from the gas supply into the apparatus and delivering thegas to the subject. Other embodiments include a method for increasingthe volume of gas delivered to a subject by providing any of thebreathing assistance devices or apparatuses described herein, adjustingthe angle of the distal end of the duct with respect to a vertical axisand releasing gas from the gas supply into the apparatus to deliver gasto the subject. In some embodiments, the distal end of the duct isadjusted to an angle greater than or equal to between about 91-170degrees. In other embodiments, the distal end of the duct is adjusted toan angle of about 135 degrees with respect to a vertical axis.

EXAMPLE 1

This example describes the ventilator system used and experimentsperformed to test the system described in FIG. 5. A lung machinemanufactured by Ingmar Medical, Pittsburgh, Pa. (www.ingmarmed.com) wasconnected at patient interface of the ventilator system. Two differentthree-port valves were tested. (a) A three-port (three-way) solenoidvalve manufactured by MAC Valves, Inc., Wixom, Mich. (www.macvalves.com)was used in the system. (b) A three-port (three-way) solenoid valvecustom made with an orifice diameter of 10 mm. The cycling of the valvewas controlled using an electronic timer made by IDEC Corporation,Sunnyvale, Calif. (us.idec.com). Compressed air and air/oxygen mixtureswere used in the tests. The tubing used was the standard 10 mm plastictubing used with conventional ventilator systems in a hospital setting.The pressure at the patient interface was measured using a manometermanufactured by Life Design Systems, Inc., Madison, Wisc. The manometerhad a range of −20 cm of water to +80 cm of water in increments of 1 cmwater. Tests were run for gas flow rates from 0.5 L/min through 5 L/minin increments of 0.5 L/min, and from 5 L/min through 15 L/min inincrements of 1 L/min. The gas flow rate was set using flowmetermanufactured by Precision Medical, Northampton, Pa(www.precisionmedical.com). Two variable pressure-relief valves wereconnected. Each variable pressure-relief valve had a rotatable knob thatallowed variation of set pressure by rotation of the knob. A scaleallowed easy and accurate adjustment of pressure setting at which apressure relief would occur. The setting of the PIP pressure-reliefvalve was varied from 10 to 30 cm of water, and the setting of the PEEPpressure relief valve was varied from 2 to 10 cm of water. The cyclingof the three-port valve was done from 1 cycle per minute to 60 cyclesper minute. Each cycle corresponds to a breath and thus the tests wereconducted from 1 breath per minute to 60 breaths per minute.

The three-port valve manufactured by MAC Valves offers a resistance toflow of gas, resulting in a loss of pressure. The loss of pressure dueto the resistance of the three-port valve increased as the flow rate ofgas was increased. At gas flow rates of 15 L/min, a pressure loss ashigh as 4 cm water was observed in the valve, resulting in a backpressure whereby observed PIP and PEEP at patient interface was about 4cm of water higher than that set by the PIP and PEEP pressure-reliefvalves. Therefore, depending on the flow rate of gas, a correction toaccount for the back pressure of the valve had to be made to the valuesof PIP and PEEP set using the pressure-relief valves. When the backpressure was 4 cm of water, a correction of 4 cm to the setting ofpressure-relief valve was made such that actual set value was 4 cm lessthan the required PIP or PEEP at the patient interface. Thus if therequired PEEP at the patient interface is 10 cm of water and the backpressure is 4 cm of water, then the set value of PEEP at thepressure-relief valve is 6 cm

Tests using the custom made three-port valve with an orifice diameter of10 mm showed that the back pressure from this three-port valve wasnegligible for the above test parameters. The back pressure from thevalve is primarily due to size the valve (e.g., diameter of valveorifice through which gas passes, diameter of inlet and outlet passageways and ports of valve) that creates resistance to flow of gas. Thesmaller the orifice size, e.g., smaller the diameter, the higher theresistance. To minimize the back pressure and the resulting correctionto set values of PIP and PEEP, the size of orifice, the size of internalpassage ways, the size of the ports are preferably the same as orsimilar to the size of the ventilator tubing. The pressure loss in thevalve can be calculated using a coefficient of flow (Cv) of the valve.The calculation method is generally known. The pressure loss decreasesas the Cv value increases. The gas is a compressible fluid and the Cvvalue and pressure loss of gas depends on temperature and pressure ofthe gas. The pressure of the gas in the ventilator system is slightlyabove atmospheric (2-50 cm of water above atmospheric) and thetemperature of the gas in the ventilator system may be kept slightlyabove room temperature and could be as high as 40 degrees Celsius. Forthe gas pressure and temperature that are generally prevalent in aventilator system, the coefficient of flow Cv of the valve is preferablygreater than about 1.5 and more preferably greater than about 2.

EXAMPLE 2

This example describes the ventilator system used and tests performedusing a system as shown in FIG. 12 wherein two two-port valves were usedto determine whether two two-port valves would replicate the system andtests done in Example 1 where a single three-port valve was used. Twotwo-port solenoid valves manufactured by MAC Valves, Inc., Wixom, Mich.were used in the system. The size of the two-port (two-way) valve wasthe same as the three-port valve manufactured by MAC Valves, Inc. thatwas used in part (a) of Example 1. The first two-port solenoid valve wasplaced on the PIP control duct and is located between the PIPpressure-relief valve and the distal end of the primary duct. The secondtwo-port solenoid valve was placed on the PEEP control duct and islocated between the PEEP pressure-relief valve and the distal end of theprimary duct. The test parameters were the same as those in Example 1.The two valves were controlled such that when the first valve was open,the second valve was closed and when the first valve was closed, thesecond valve was open. The two two-port valves were identical and theirsize including valve orifice and port diameters was the same as that ofthe three-port MAC valve used in part (a) of Example 1. The observedperformance of the system in Example 2 was similar to the performance ofthe system in Example 1 when MAC valve was used.

There has thus been described a medically and commercially useful methodand apparatus for providing breathing support. It is appreciated thatthough described for a patient, the method and apparatus can be used bya healthy mammal to enhance breathing. It will be appreciated thatwell-known structures, devices, and operations have been shown in blockdiagram form or without detail in order to avoid obscuring theunderstanding of the description. Where considered appropriate,reference numerals or terminal portions of reference numerals have beenrepeated among the figures to indicate corresponding or analogouselements, which may optionally have similar characteristics. Theparticular embodiments described are not provided to limit theinvention, but to illustrate it. Further, as the following claimsreflect, inventive aspects may lie in less than all features of a singledisclosed embodiment. In another situation, an inventive aspect mayinclude a combination of embodiments described herein or in acombination of less than all aspects described in a combination ofembodiments. Thus, the claims following the Detailed Description arehereby expressly incorporated into this Detailed Description, with eachclaim standing on its own as a separate embodiment of the invention.

1. An apparatus to provide breathing support to a patient comprising: athree-port valve comprising at least three ports, said three portscomprising an inlet port, a first outlet port and a second outlet port,the inlet port adapted for connection to a patient interface via aprimary duct configured for flow of a gas; at least one peak inspiratorypressure (PIP) control duct connected to the first outlet port of thevalve; at least one positive end-expiratory pressure (PEEP) control ductconnected to the second outlet port of the valve; at least one PIPpressure-relief valve connected to the PIP control duct; wherein thethree-port valve is configured to cycle between the first outlet portand the second outlet port thereby switching the flow of the gas fromthe inlet port to only the first outlet port and from the inlet port toonly the second outlet port.
 2. The apparatus of claim 1 furthercomprising at least one PEEP pressure-relief valve connected to the PEEPcontrol duct.
 3. The apparatus of claim 1 wherein the pressure-reliefvalve is a variable pressure-relief valve.
 4. The apparatus of claim 1further comprising a container containing a body of fluid, wherein thePEEP control duct is configured to be immersed in the body of fluid inthe container.
 5. The apparatus of claim 1 wherein a cycle correspondsto one breath and when the gas flows from the inlet port to the firstoutlet port of the three-port valve, the gas flows through the PIPcontrol duct, thereby controlling a PIP in the apparatus so that thepatient receives the PIP, and when the gas flows from the inlet port tothe second outlet port of the three-port valve, the gas in the apparatusflows through the PEEP control duct, thereby lowering pressure in theapparatus to a PEEP so that the patient receives the PEEP.
 6. Theapparatus of claim 1 further comprising at least one safety duct adaptedfor connection to the primary duct and configured to be connected to asafety pressure-relief valve.
 7. The apparatus of claim 1 furthercomprising at least one controller communicably connected to thethree-port valve to control a rate of cycling of the valve, therebycontrolling a number of breaths per minute, and to control at least oneof (a) an inspiratory time in seconds, (b) a ratio of the inspiratorytime to an expiratory time, and (c) the inspiratory time as a percentageof a cycle time, thereby maintaining the ratio of the inspiratory timeto the expiratory time as determined by a user.
 8. The apparatus ofclaim 7 wherein the PIP pressure-relief valve is communicably connectedto the controller.
 9. The apparatus of claim 1 wherein the three-portvalve has a coefficient of flow Cv greater than about 1.5.
 10. Theapparatus of claim 1 wherein the three-port valve is a solenoid valve.11. An apparatus to provide breathing support to a patient comprising: athree-port valve comprising at least three ports, said three portscomprising an inlet port, a first outlet port and a second outlet port,the inlet port adapted for connection to a patient interface via aprimary duct configured for a flow of a gas; at least one peakinspiratory pressure (PIP) control duct connected to the first outletport of the valve; at least one positive end-expiratory pressure (PEEP)control duct connected to the second outlet port of the valve; at leasttwo pressure-relief valves wherein a first pressure-relief valve isconnected to the PIP control duct and a second pressure-relief valve isconnected to the PEEP control duct; wherein the three-port valve isconfigured to cycle between the first outlet port and the second outletport thereby switching the flow of the gas from the inlet port to onlythe first outlet port and from the inlet port to only the second outletport; wherein a cycle corresponds to one breath; and wherein when thegas flows from the inlet port to the first outlet port of the three-portvalve, the gas flows through the PIP control duct, thereby controlling aPIP in the apparatus so that the patient receives the PIP, and when thegas flows from the inlet port to the second outlet port of thethree-port valve, the gas in the apparatus flows through the PEEPcontrol duct, thereby lowering pressure in the apparatus to a PEEP sothat the patient receives the PEEP.
 12. The apparatus of claim 11further comprising at least one safety duct adapted for connection tothe primary duct and configured to be connected to a third pressurerelief valve.
 13. The apparatus of claim 11 further comprising at leastone controller communicably connected to the three-port valve to controla rate of cycling of the valve, thereby controlling a number of breathsper minute, and to control at least one of (a) an inspiratory time inseconds, (b) a ratio of the inspiratory time to an expiratory time, and(c) the inspiratory time as a percentage of a cycle time, therebymaintaining the ratio of the inspiratory time to the expiratory time asdetermined by a user.
 14. The apparatus of claim 13 wherein the PIPpressure-relief valve and the PEEP pressure-relief valve arecommunicably connected to the controller.
 15. The apparatus of claim 11wherein the three-port valve has a coefficient of flow Cv greater thanabout 1.5.
 16. The apparatus of claim 11 wherein the three-port valve isa solenoid valve.
 17. The apparatus of claim 11 further comprising apressurized gas supply.
 18. The apparatus of claim 11 wherein the PIPpressure-relief valve and the PEEP pressure relieve valve areelectro-mechanical valves.
 19. The apparatus of claim 11 wherein atleast one pressure-relief valve selected from a group of the PIPpressure-relief valve and the PEEP pressure relieve valve is amechanical valve.
 20. The apparatus of claim 11 wherein at least onepressure-relief valve selected from a group of the PIP pressure-reliefvalve and the PEEP pressure-relief valve comprises a knob to vary thepressure at which a relief of pressure will occur.